|Publication number||US8029449 B2|
|Application number||US 12/862,485|
|Publication date||Oct 4, 2011|
|Filing date||Aug 24, 2010|
|Priority date||Aug 18, 2000|
|Also published as||CA2518444A1, DE602004030097D1, EP1603475A2, EP1603475A4, EP1603475B1, US6955174, US7780608, US20040002749, US20060015092, US20100318075, WO2004080280A2, WO2004080280A3|
|Publication number||12862485, 862485, US 8029449 B2, US 8029449B2, US-B2-8029449, US8029449 B2, US8029449B2|
|Inventors||James Joye, Kristine Tatsutani, Joseph J. Williams|
|Original Assignee||Boston Scientific Scimed, Inc.|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (52), Non-Patent Citations (6), Classifications (32), Legal Events (2)|
|External Links: USPTO, USPTO Assignment, Espacenet|
This application is a continuation of U.S. patent application Ser. No. 11/228,691 filed Sep. 16, 2005, now U.S. Pat. No. 7,780,608, which is a divisional patent application which claims priority from U.S. patent application Ser. No. 10/387,347 filed on Mar. 11, 2003, now U.S. Pat. No. 6,955,174, which is a continuation-in-part of U.S. patent application Ser. No. 09/641,462 filed Aug. 18, 2000, now U.S. Pat. No. 6,602,246, the full disclosures of which are incorporated herein by reference.
1. Field of the Invention
The present invention relates generally to methods, apparatus, and kits for treating blood vessels. More particularly, the present invention provides methods, apparatus, and kits for identifying and/or treating a lesion. In one exemplary embodiment, the invention provides devices which are particularly useful for identification and treatment of vulnerable atherosclerotic plaque within a patient's vasculature to inhibit harmful releases within the vasculature, such as those which may be responsible for strokes or acute coronary syndromes of unstable angina, myocardial infarction, and sudden cardiac death.
Atherosclerotic plaque is present to some degree in most adults. Plaques can severely limit the blood flow through a blood vessel by narrowing the open vessel lumen. This narrowing effect or stenosis is often responsible for ischemic heart disease. Fortunately, a number of percutaneous intravascular procedures have been developed for treating atherosclerotic plaque in a patient's vasculature. The most successful of these treatments may be percutaneous transluminal angioplasty (PTA). PTA employs a catheter having an expansible distal end, usually in the form of an inflatable balloon, to dilate a stenotic region in the vasculature to restore adequate blood flow beyond the stenosis. Other procedures for opening stenotic regions include directional atherectomy, laser angioplasty, stents, and the like. Used alone or in combination, these percutaneous intravascular procedures have provided significant benefits for treatment of stenosis caused by plaque.
While treatments of stenosis have advanced significantly over the last few decades, the morbidity and mortality associated with vascular plaques have remained significant. Recent work suggests that plaque may generally fall into one of two different general types: standard stenotic plaques and vulnerable plaques. Stenotic plaque, which is sometimes referred to as thrombosis-resistant plaque, can generally be treated effectively by the known intravascular lumen opening techniques mentioned above. Although the stenosis they induce may benefit from treatment, these atherosclerotic plaques themselves are often a benign and effectively treatable disease.
Unfortunately, as plaque matures, narrowing of a blood vessel by a proliferation of smooth muscle cells, matrix synthesis, and lipid accumulation may result in formation of a plaque which is quite different than a standard stenotic plaque. Such atherosclerotic plaque often becomes thrombosis-prone, and can be highly dangerous. This thrombosis-prone or vulnerable plaque may be a frequent cause of acute coronary syndromes.
The characterization of these vulnerable (and potentially life-threatening) plaques is currently under investigation. A number of strategies have been proposed to detect a vulnerable plaque. Proposed strategies include angiography, intravascular ultrasound, angioscopy, magnetic resonance imaging, magnetic resonance diffusion imaging, spectroscopy, infrared spectroscopy, scintigraphy, optical coherence tomography, electron beam computed tomographic scanning, and thermography, all of which have had limited success. In particular, proposed thermography methods detect temperature variations, as vulnerable plaque is typically inflamed and as such gives off more heat than standard stenotic plaque. While current thermography methods show promise, they continue to suffer from limited temperature sensitivity which may often result in inaccurate detections of vulnerable plaque.
While the known procedures for treating plaque have gained wide acceptance and shown good efficacy for treatment of standard stenotic plaques, they may be ineffective (and possibly dangerous) when thrombotic conditions are superimposed on atherosclerotic plaques. Specifically, mechanical stresses caused by primary treatments like PTA or stenting may actually trigger release of fluids and/or solids from a vulnerable plaque into the blood stream, thereby potentially causing a coronary thrombotic occlusion.
For these reasons, it would be desirable to provide methods, apparatus, and kits for the detection and treatment of vulnerable plaque in blood vessels. The methods and apparatus should be suitable for intravascular and intraluminal introduction, preferably via a percutaneous approach. It would be particularly desirable if the new methods and apparatus were able to detect the vulnerable plaque accurately and/or deliver the treatment in a very controlled and safe manner, with minimal deleterious effects on adjacent tissues. Treatment methods, apparatus, and kits should further be effective in inhibiting release of the vulnerable plaque with minimum side effects. At least some of these objectives will be met by the invention described herein.
2. Description of the Background Art
A cryoplasty device and method are described in PCT Publication No. WO 98/38934. Balloon catheters for intravascular cooling or heating a patient are described in U.S. Pat. No. 5,486,208 and WO 91/05528. A cryosurgical probe with an inflatable bladder for performing intrauterine ablation is described in U.S. Pat. No. 5,501,681. Cryosurgical probes relying on Joule-Thomson cooling are described in U.S. Pat. Nos. 5,275,595; 5,190,539; 5,147,355; 5,078,713; and 3,901,241. Catheters with heated balloons for post-angioplasty and other treatments are described in U.S. Pat. Nos. 5,196,024; 5,191,883; 5,151,100; 5,106,360; 5,092,841; 5,041,089; 5,019,075; and 4,754,752. Cryogenic fluid sources are described in U.S. Patent Nos. 5,644,502; 5,617,739; and 4,336,691. The following U.S. Patents may also be relevant to the present invention: U.S. Pat. Nos.5,458,612; 5,545,195; and 5,733,280.
Thermography is described by Ward Casscells, et al. in The Vulnerable Atherosclerotic Plaque: Understanding. Identification, and Modification, Chpt. 13, pp. 231-242 (1999); and in L. Diamantopoulos, et al. at the following Internet address: http://www.eurekalert.org/releases/ahaati041499.html. The impact of low temperatures on lipid membranes is described by Jack Kruuv in an article entitled Advances in Molecular and Cell biology, vol. 19, pp. 143-192 (1997); P. J. Quinn in Cryobiology. Vol. 22, pp. 128-146 (1985); and Michael J. Taylor, Ph.D. in Biology Of Cell Survival In The Cold, (Harwood Academic Publishers, In Press).
The full disclosures of each of the above references are incorporated herein by reference.
The present invention provides detection and treatment of vulnerable plaque within a blood vessel of a patient. The blood vessel may be any blood vessel in the patient's vasculature, including veins, arteries, and particularly coronary arteries. The vessel will typically be partially stenosed, at least in part from vulnerable plaque. In particular, the present invention may inhibit release of retained fluid within the vulnerable plaque so as to inhibit acute coronary syndrome and to help maintain the patency of a body lumen. The present invention may also provide for the treatment of vulnerable plaque in carotid arteries for stroke prevention. Where the patient's vasculature has both the vulnerable plaque and standard stenotic plaque, the treatment techniques described herein may be selectively directed to the vulnerable plaque, optionally without substantial cooling of the standard stenotic plaque. In other embodiments, both types of plaque may be treated.
In a first aspect, the present invention provides a method for treating vulnerable plaque of a blood vessel. The method comprises cooling the vulnerable plaque to a temperature sufficient to inhibit release of retained fluid from within the vulnerable plaque into the blood stream. The cooling treatment will often be directed against all or a portion of a circumferential surface of a lumen of the blood vessel, and will preferably inhibit release of lipid-rich liquid being releasably retained by the vulnerable plaque.
Optionally, a portion of the vasculature may be identified in which releasing of the retained fluid should be inhibited. For example, releasing of the retained fluid from a vulnerable plaque in some cardiac arteries may result in sudden cardiac death. Releasing of the retained fluid from a vulnerable plaque in the carotid arteries may result in stroke. Hence, when it is determined that a plaque is located within such a portion of the vasculature, the cooling step may be performed at this identified plaque location. Optionally, such cooling may be performed without specifically identifying the plaque as a vulnerable plaque. In other embodiments, the vulnerable plaque may be differentiated from standard stenotic plaque, often prior to initiation of the cooling. Hence, the cooling may be selectively directed at vulnerable plaque, rather than being applied to plaque in general. Advantageously, a single balloon catheter may be used to both differentiate and treat the vulnerable plaque.
Differentiation of vulnerable plaque from standard stenotic plaque may be enhanced by the use of a balloon catheter inflated with a gas. The differentiation may be effected using a temperature sensor for sensing a temperature of a tissue adjacent the balloon. Surprisingly, plaque differentiation benefits from gas temperatures within the balloon of about 20° C. or more, preferably being 30° C. or more. Hence, the balloon may be inflated so that an initial temperature of the gas within the balloon is about 30° C. Inflation with such a warm gas can amplify the measured temperature differences (for example) sensed by temperature sensors distributed along a balloon wall and in thermal engagement with the vulnerable plaque (at a first sensor) and a standard stenotic plaque or healthy luminal wall (at a second sensor).
Cooling of the vessel may be effected by introducing a catheter into a lumen of the blood vessel. A first balloon is positioned within the vessel lumen adjacent the vulnerable plaque. Cryogenic cooling fluid is introduced into the first balloon and exhausted. A second balloon disposed over the first balloon is expanded to radially engage the vessel lumen. Generally, the temperature of an inside surface of the first balloon will be in the range from about −55° C. to −75° C. and an outside surface of the first balloon will be in the range from about −25° C. to −45° C. The temperature of an outside surface of the second balloon will be in the range from about 10° C. to −40° C., preferably from about 10° C. to −20° C., more preferably from about 5° C. to −10° C. In alternative embodiments, the temperature of an inside surface of the first balloon may be in a range from about −30 C to −50 C, and an outside surface of the first balloon may be in a range from about −20 C to −40 C.
Usually, the temperature at the surface of the blood vessel lumen is in the range from about 10° C. to −40° C., preferably from about 10° C. to −20° C., more preferably from about 5° C. to −10° C. The tissue is typically maintained at the desired temperature for a time period in the range from about 15 seconds to 120 seconds, preferably from 30 seconds to 60 seconds, optionally being in a range from about 20 seconds to about 60 seconds. Vulnerable plaque stabilization may be enhanced by repeating cooling in cycles, typically with from about 1 to 3 cycles, with the cycles being repeated at a rate of about one cycle every 120 seconds.
Surprisingly, cooling temperatures above 0° C. can effect a transition of the vulnerable plaque's lipid core from a disordered cystalline state fluid to a ordered crystalline state solid or gel. Thus, vulnerable plaque can be stabilized by cooling the lipid-rich liquid sufficiently to change a state of the lipid-rich liquid, typically to a highly ordered hexagonal lattice at transition temperatures generally in the range from about 10° C. to −10° C. The stabilization may, at least in part, remain in effect after subsequent return of the tissue to a normal body temperature. The stabilization may, at least in part, be transitory, with the stabilization effect diminishing and/or disappearing after cooling is terminated. The vulnerable plaque may be treated while it remains at least partially stabilized.
Advantageously, the cooling may be accurately controlled to tailor a desired tissue response. Cooling may be performed so as to cause apoptosis and/or necrosis in the tissues comprising or adjacent to the vulnerable plaque. Alternatively, the cooling may also be performed in a manner that avoids causing apoptosis and/or necrosis. Cooling may stabilize the vulnerable plaque while inhibiting necrosis and/or apoptosis of tissue adjacent the lipid-rich liquid, particularly of the tissues defining a cap of cells between the lipid-rich liquid and the lumen of the blood vessel. Cooling may also inhibit inflammation and deterioration of the vulnerable plaque. The cooling treatment may further inhibit rupture of the cap of cells of the vulnerable plaque.
In other aspects, the present invention of cooling the vulnerable plaque to inhibit release of lipid-rich liquid may be combined with additional treatments. For example, one adjunctive method may comprise treating the cooled vulnerable plaque with a primary treatment. Suitable primary treatments may include balloon angioplasty, atherectomy, rotational atherectomy, laser angioplasty, or the like, where the lumen of the treated blood vessel is enlarged to at least partially alleviate a stenotic condition. The primary treatment may also include procedures for controlling restenosis, such as stent placement. In the case of arteries, the primary treatment will be effected shortly before, during, or preferably very shortly after the cooling treatment, preferably within 60 seconds of the cooling treatment, more preferably immediately following the cooling of the lipid-rich liquid to a desired temperature. Alternatively, cooling methods may additionally comprise passivating the vulnerable plaque by reducing a size of the lipid-rich liquid, changing a cellular consistency or composition of the lipid-rich liquid, enhancing a structural integrity of the cap (e.g. increasing a thickness of the cap), modifying a cellular composition or structural properties of the cap, and/or the like by altering the chemistry or life cycle of the vulnerable plaque.
In another aspect, the present invention provides a method for treating vulnerable plaque of a blood vessel, the vulnerable plaque releasably retaining fluid. The method includes detecting the vulnerable plaque with a balloon catheter and cooling the vulnerable plaque with the balloon catheter to a temperature sufficient to inhibit release of the retained fluid into the blood vessel.
Preferably, the detecting step will comprise inflating a balloon of the balloon catheter so that a gas within the balloon is at a temperature of 30° C. or more. The cooling step may comprise cooling an outer surface of the balloon to a temperature of about 10° C. or less.
In another aspect, the present invention provides a method for detecting vulnerable plaque of a blood vessel. The method includes positioning a balloon within the vessel lumen adjacent a plaque. The balloon is inflated so that a plurality of temperature sensors affixed to the balloon are coupled to a surface of the vessel lumen. A temperature differential along the lumen surface is sensed with the sensors.
The inflating step may be performed so that the gas within the balloon has a temperature of about 20° C. or more, the balloon preferably being inflated so that the gas has an initial temperature in the balloon of 30° C. or more. Surprisingly, temperature sensors along the balloon wall can detect a temperature differential of greater than about 1° C. between a vulnerable plaque and an adjacent portion of the luminal wall with such a system. Additionally, the size of the “hot” region disposed along the vessel wall may increase when the balloon is inflated with the gas. Hence, the use of a warm gas within a balloon catheter can act to amplify the sensitivity of the system for detection of vulnerable plaques.
In another aspect, the present invention provides a cryotherapy catheter for detecting and treating vulnerable plaque of a blood vessel having a lumen surface. The catheter generally comprises a catheter body having a proximal end and a distal end with a cooling fluid supply lumen and an exhaust lumen extending therebetween. A first balloon is disposed near the distal end of the catheter body in fluid communication with the supply lumen and exhaust lumen. A second balloon is disposed over the first balloon with a thermal barrier therebetween. A plurality of temperature sensors are affixed to the second balloon so as to provide temperature measurements of the lumen surface.
In another aspect, the present invention provides a catheter for detecting a vulnerable plaque of a blood vessel having a lumen surface. The catheter generally comprises a catheter body having a proximal end and a distal end with a supply lumen and an exhaust lumen extending therebetween. A balloon is disposed on the distal end of the catheter body in fluid communication with the supply lumen and exhaust lumen. A plurality of temperature sensors are supported by the balloon so as to provide temperature measurements of the lumen surface.
Optionally, an inflation supply may be in fluid communication with the supply lumen at the proximal end of the catheter body. The inflation supply may be configured to inflate the balloon with a gas when detecting the vulnerable plaque. The gas in the balloon may have a temperature of about 20° C. or more during the temperature measurements. In some embodiments, the inflation supply may further be configured to direct cooling fluid to the balloon in a treatment mode so that an outer temperature of the balloon is about 10° C. or less.
In another aspect, the invention also provides a kit for treating vulnerable plaque in a blood vessel. The kit comprises a catheter having a proximal end, a distal end, and a cooling member near its distal end. Instructions are included in the kit for use of the catheter. These instructions comprise the step of cooling the blood vessel adjacent the vulnerable plaque to inhibit release of the retained fluid into the blood vessel. Such a kit may include instructions for any of the methods described herein.
In yet another aspect, the invention provides a kit for detecting vulnerable plaque of a blood vessel. The kit comprises a catheter having a proximal end, a distal end, and a balloon member with a plurality of temperature sensors near its distal end. Instructions are included in the kit for use of the catheter. These instructions comprise the steps of positioning a balloon within the vessel lumen adjacent a plaque, inflating the balloon so that a plurality of temperature sensors affixed to the balloon are coupled to a surface of the vessel lumen, and sensing a temperature differential along the lumen surface with the sensors. Such a kit may include instructions for any of the methods described herein.
As used herein, the terms “vulnerable plaque” and “hot plaque” refer to atherosclerotic plaque that is thrombosis-prone.
Three determinants of vulnerability are illustrated in
Referring now to
The balloons 22, 24 may be an integral extension of the catheter body 12, but such a structure is not required by the present invention. The balloons 22, 24 could be formed from the same or a different material as the catheter body 12 and, in the latter case, attached to the distal end 16 of the catheter body 12 by suitable adhesives, heat welding, or the like. The catheter body 12 may be formed from conventional materials, such as polyethylenes, pebax, polyimides, and copolymers and derivatives thereof. The balloons 22, 24 may also be formed from conventional materials used for angioplasty, preferably being inelastic, such as polyethylene terephthalate (PET), polyethylene, pebax, or other medical grade material suitable for constructing a strong non-distensible balloon. Additionally, balloons 22 and 24 could be formed from different material to provide improved protection. For example, the first balloon 22 could be formed from PET to provide strength while the second balloon 24 could be formed from polyethylene to provide durability. The balloons 22, 24 have a length of at least 1 cm each, more preferably in the range from 2 cm to 5 cm each. The balloons 22, 24 will have diameters in the range from 2 mm to 5 mm each in a coronary artery and 2 mm to 10 mm each in a peripheral artery.
The thermal barrier 26 may comprise a gap maintained between the balloons 22, 24 by a filament. The filament typically comprises a helically wound, braided, woven, or knotted monofilament. The monofilament may be formed from PET or polyethylene napthlate (PEN), and affixed to the first balloon 22 by adhesion bonding, heat welding, fasteners, or the like. The thermal barrier 26 may also comprise a gap maintained between the balloons 22, 24 by a plurality of bumps on an outer surface of the first balloon 22 and/or an inner surface of the second balloon 24. The plurality of bumps may be formed in a variety of ways. For example, the bumps may be intrinsic to the balloon (created during balloon blowing), or the bumps could be created by deforming the material of the balloon wall, by affixing mechanical “dots” to the balloon using adhesion bonding, heat welding, fasteners, or the like. Alternatively, the thermal barrier 26 may comprise a gap maintained between the balloons 22, 24 by a sleeve. The sleeve may be perforated and formed from PET or rubbers such as silicone and polyurathane. Still further structures might be employed to maintain a gap between the balloons, including a liquid.
Hubs 34 and 36 are secured to the proximal end 14 of the catheter body 12. Hub 34 provides a port 38 for connecting a cryogenic fluid source to the fluid supply lumen 18 which is in turn in fluid communication with the inner surface of the first balloon 22. Hub 34 further provides a port 40 for exhausting the cryogenic fluid which travels from balloon 22 in a proximal direction through the exhaust lumen 20. Hub 36 provides a port 42 for a guidewire which extends through a guidewire lumen 44 in the catheter body 12. Typically, the guidewire lumen 44 will extend through the exhaust lumen 20, as shown in
The cryotherapy catheter 10 in
The vacuum space 52 may be provided by a simple fixed vacuum chamber 64 coupled to the vacuum space 52 by a vacuum lumen 66 of the body 12 via a vacuum port 68 (See
An audio alert or buzzer 76 may be located on the handle 74, with the buzzer providing an audio warning unless the handle is maintained sufficiently upright to allow flow from the fluid supply 62. The cryotherapy catheter may additionally comprise a hypsometer 72 coupled to the volume by a thermistor, thermocouple, or the like located in the first balloon 22 or handle to determine the pressure and/or temperature of fluid in the first balloon 22. The hypsometer allows for accurate real time measurements of variables (pressure, temperature) that effect the efficacy and safety of cryotherapy treatments.
The dual balloon cryotherapy catheter 10 in
Detection of vulnerable plaque may be carried out by introducing the cryotherapy catheter 10 into a lumen 104 of the blood vessel 100 over a guidewire. The first balloon 22 is positioned within the blood vessel lumen 104 adjacent a plaque. The first balloon 22 is inflated so that the plurality of temperature sensors 78 affixed to the second balloon 24 (which expands upon inflation) thermally couple a surface of the vessel lumen. A temperature differential along the lumen surface 105 is sensed with the sensors. Inflation of balloon 22 may be effected by a gas, such as carbon dioxide, nitrous oxide, or the like, at a pressure in the range from about 5 psi to 50 psi. As used herein, “psi” encompasses pounds per square inch above ambient pressure, sometimes referred to as “psig.” The balloon 22 will typically be inflated for a time period in the range from 10 to 120 seconds. The balloon catheter may sense for a temperature differential in a static position or as it moving along the lumen surface. Advantageously, temperature sensors 78 thermally engage the lumen surface to allow for direct temperature measurements to be made at specific locations along the lumen surface. This increased temperature sensitivity may in turn lead to improved temperature mapping and accurate vulnerable plaque detections. Cryotherapy catheter 10 may then be used for treating the detected vulnerable plaque as described in more detail below with reference to
An alternative catheter 10′ for detecting a vulnerable plaque of a blood vessel having a lumen surface is illustrated in
Detection of vulnerable plaque may be carried out by introducing the detection catheter 10′ into a lumen 104 of the blood vessel 100 over a guidewire. The balloon 86 is positioned within the vessel lumen adjacent a plaque. The balloon 86 is inflated so that a plurality of temperature sensors 78 affixed to the balloon thermally couple a surface of the vessel lumen. A temperature differential along the lumen surface is sensed with the sensors. Balloon 86 is generally inflatable with standard inflation media, such as contrast, saline, or the like. An inflation media supply and/or exhaust port 90 is connected to the supply and/or exhaust lumen 88 which is in turn in fluid communication with the inner surface of balloon 86. Balloon 86 will typically be inflated for a time period in the range from 10 to 120 seconds. The balloon catheter may sense for a temperature differential in a static position or as it moving along the lumen surface.
Referring now to
Suitable cryogenic fluids will preferably be non-toxic and may include liquid nitrous oxide, liquid carbon dioxide, cooled saline and the like. The cryogenic fluid will flow through the supply lumen 18 as a liquid at an elevated pressure and will vaporize at a lower pressure within the first balloon 22. For nitrous oxide, a delivery pressure within the supply lumen 18 will typically be in the range from 600 psi to 1000 psi at a temperature below the associated boiling point. After vaporization, the nitrous oxide gas within the first balloon 22 near its center may have a pressure in the range from 15 psi to 100 psi, optionally having a pressure in a range from 50 to 150 psi. The nitrous oxide gas may have a pressure in the range from 50 psi to 100 psi in a peripheral artery, preferably having a pressure in a range from 100 to 150 in a peripheral artery, and may have a pressure in a range from about 15 psi to 45 psi in a coronary artery, preferably having a pressure in a range from 100 to 150 psi in a coronary artery.
The temperature of an inside surface of the first balloon may be in the range from about −55° C. to −75° C. (preferably being in a range from about −30 C to −50 C) and an outside surface of the first balloon may be in the range from about −25° C. to −45° C. (preferably being in a range from about −20 C to −40 C). The temperature of an outside surface of the second balloon will be in the range from about 10° C. to −40° C., preferably from about 10° C. to −20° C., more preferably from about 5° C. to −10° C. This will provide a desired treatment temperature in a range from about 10° C. to −40° C., preferably from about 10° C. to −20° C., more preferably from about 5° C. to −10° C. The tissue is typically maintained at the desired temperature for a time period in the range from about 15 to 120 seconds, optionally being from 30 to 60 seconds, preferably being from 20 to 60 seconds.
Vulnerable plaque stabilization may be enhanced by repeating cooling in cycles, typically with from about 1 to 3 cycles, with the cycles being repeated at a rate of about one cycle every 120 seconds.
In some instances, cooling of the vessel may be limited to inhibit or avoid necrosis and/or apoptosis of tissue adjacent the lipid-rich liquid, particularly of the tissues defining a cap of cells 108 between the lipid-rich liquid 106 and the lumen of the blood vessel 104 (see
In other applications, cooling of the vessel at cooler temperatures may be desirable to provide for or induce apoptosis and/or programmed cell death stimulation of inflammatory cells (e.g. macrophages 118, see
Referring now to
With reference now to
A kit 126 including a catheter 10 and instructions for use 128 is illustrated in
Referring now to
Heat transfer coefficients for thermal flows between hot plaque 202 and surrounding tissues can be modeled using known thermal properties of the tissue and/or by measuring the properties of appropriate human, animal or model tissues. Similarly, heat flow through luminal surface end 208 of hot plaque 202 may be based on known or measured heat transfer properties. The thermal model results described below make use of a heat transfer coefficient directly between a hot plaque surface 208 and a blood flow 210 within the lumen of 0.000594 W/mm2−° C.
Referring now to
Referring now to
The fluid 210 of the thermal model 200 within the balloon was assumed to be water or nitrous oxide gas. Temperatures were assumed to be measured at a temperature sensor 216 disposed between balloon layers 212, 214, with the exemplary temperature sensor location being disposed at a radius of 0.583 mm from the hot plaque center so as to result in a starting surface temperature of approximately 38° C. Temperature of the temperature sensor versus time was determined (see
Referring now to
Referring now to
As would be expected, when a normal tissue site (having an initial temperature of 37° C.) is engaged by a balloon filled with water or nitrous oxide gas at 37° C., the temperature sensors indicates a constant 37° C. When a hot plaque is engaged with a water-filled balloon, the temperature sensor indicates an increasing temperature. While the initial surface of the hot plaque was 38° C., the reading from the water-filled balloon in
Referring now to
In general, thermal model 200 indicates a greater different between hot plaque luminal surface temperatures and normal plaque or healthy luminal surface tissue temperatures after balloon inflation. A larger difference in these temperatures can result in a higher detection sensitivity. The absolute value of the surface temperature after balloon inflation was also evaluated, as higher surface temperatures also produce a higher differentiation sensitivity. Per both of these evaluation criteria, the gas-filled balloon performance exceeded that of the liquid-filled balloon performance particularly when relatively warm gases were used within the balloon. Specifically, under the thermal model analyses, the gas-filled balloon resulted in a higher difference between the measured hot plaque surface temperature and the measured normal plaque surface temperature, with the temperature differences using a gas-filled balloon being approximately twice those resulting from a liquid-filled balloon. Additionally, the absolute measured hot plaque surface temperature was uniformly higher when a gas-filled balloon was modeled as compared to a water-filled balloon.
While the above is a complete description of the preferred embodiments of the invention, various alternatives, modifications, and equivalents will be obvious to those of skill in the art. Hence, the above description should not be taken as limiting the scope of the invention which is defined by the appended claims.
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|U.S. Classification||600/549, 606/21|
|International Classification||A61B18/02, A61B5/01, A61B17/22, A61B17/00, A61B5/00, A61B1/12, A61B, A61B18/18|
|Cooperative Classification||A61B2017/00084, A61B2017/22051, A61B5/015, A61B2018/0262, A61B5/01, A61B18/02, A61B2017/22001, A61B5/6853, A61B1/128, A61B2017/22002, A61B2018/0022, A61B2018/0212, A61B1/12, A61B2017/00101, A61B1/3137, A61B1/00082|
|European Classification||A61B18/02, A61B5/01, A61B5/68D1H1, A61B1/00E4H1, A61B5/01B, A61B1/12G|
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Owner name: SILIOS TECHNOLOGIES, FRANCE
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|Mar 18, 2015||FPAY||Fee payment|
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